JP5739927B2 - Transmitted light detection type skin fluorescence measurement device - Google Patents

Description

  The present invention measures skin autofluorescence from advanced glycation end products (AGE) accumulated in the skin to evaluate various skin diseases such as diabetes. It is related with the fluorescence measuring apparatus which can measure.

Recently, various facilities using light have been developed for diagnosing and treating diseases, and in particular, various diseases are diagnosed using fluorescence of the skin that appears outside the skin by excitation light emitted from a light source. Devices are being developed and used.
Such fluorescence is absorbed by the skin and is emitted again to the outside of the skin, and because it has biological information inside the skin, it acts as a biomarker for disease, Thereby, it is possible to grasp whether or not the physiological state of all the organs of the body has been damaged by using a non-invasive method.

For example, advanced glycation end products (AGE) are the result of Maillard reaction and are due to the oxidation of body organ proteins. This reaction damages the function of many proteins. Oxidative stress due to acute diseases such as sepsis as well as exposure to risk factors for heart disease such as smoking, high fatty acid intake, or hypercholesterolemia ), The final glycation product (AGE) is generated. Such final glycation products (AGE) are slowly degraded and accumulated over the entire time. Increases in final glycation products (AGE) are associated with the progression of chronic diseases such as atherosclerosis and tend to accumulate in the body over the lifetime of a person.
In a long-term hyperglycemic state, non-enzymatic glycation and oxidation reactions of proteins continue to occur, thereby causing an advanced glycation end product that is a complex of irreversible sugar and protein (Advanced Glycation End products). AGE) is formed. Accumulation of the final glycation product (AGE) proceeds very rapidly in people with vascular diseases such as diabetes, renal failure, cardiovascular disease. The product of the final glycation product (AGE) accumulates in various tissues including the skin. The final glycation product (AGE) has the property of emitting autofluorescence (AF) in the blue spectral region (maximum near 440 nm) upon irradiation with excitation light in the ultraviolet region (maximum near 370 nm).

As is well known, the final glycation product (AGE) serves as a biomarker for certain diseases, and by measuring skin autofluorescence using a non-invasive method, It is possible to evaluate whether the physiological state of all organs of the above has been damaged. Thus, the final glycation product (AGE) predicts long-term complications in age-related diseases. Specifically, the amount of skin autofluorescence increases from patients with diabetes and renal failure and has an effect on the progression of vascular complications and coronary heart disease (CHD) Effect. Since accumulation of such final glycation product (AGE) can be detected non-invasively by detecting by skin autofluorescence, diabetes and final glycation product (AGE) accumulate when used as a noninvasive clinical device. Effective in assessing the risk of causing long-term vascular complications in the environment.
As a method and equipment proposed for evaluating the final glycation product (AGE) by measuring skin autofluorescence (AF), Patent Document 1 discloses measuring the skin fluorescence of the patient's lower arm and measuring the final glycation product (AGE). We propose a technique to evaluate

In Patent Document 1, the excitation light source is a black glass fluorescent tube that emits light in the ultraviolet region of the wavelength range of 300 to 420 nm. Light collection and recording is performed by an optical fiber spectrometer. In order to increase the measurement area, the end face of the optical fiber is arranged at a certain distance (d: 5-9 mm) from the transparent window of the equipment, and in order to reduce the influence of the reflected light reflected from the skin, the optical fiber is It was set at an angle of about 45 ° to the surface.
Specifically, in Patent Document 1, in order to increase the light collection area, the end face of the optical fiber that collects light is arranged as far as possible from the target site, and the area of the target site measured in this case is about 0.4 cm ² .
In this case, the measurement distance (d) is increased in order to increase the area of the measurement target part, but there is a problem that the fluorescence signal collected by this increases greatly. Therefore, the conventional patent document 1 has a problem that reliability in data detection is lowered due to a limit of a measurable skin area. In particular, such accuracy problems are further reduced due to inhomogeneities on the skin, such as spots on the skin, blood vessels, and wounds.
On the other hand, Patent Document 2 discloses a device for measuring a final glycation product (AGE) in order to perform a screen test of a diabetic patient. The equipment of Patent Document 2 performs fluorescence measurement of the lower skin using an optical fiber spectrometer as in Patent Document 1. However, unlike Patent Document 1, in Patent Document 2, the optical fiber probe is configured in the form of a bundle including a plurality of branch lines.

In the apparatus according to Patent Document 2, ultraviolet rays and blue light emitted from a light emitting diode are irradiated to the lower arm of a subject through an optical fiber probe, and skin fluorescence and diffuse reflection light emitted therefrom are collected through the probe. The collected light is chromatically dispersed by a spectroscope and sensed by a linear array detector. Two of the branch lines of the optical fiber probe (illumination fibers, channel 1 and channel 2) serve to irradiate light to the target site, and the third branch line (collection fibers) transmits light emitted from the target in multiple channels. Transmit to the spectrometer. The end surface of the joint interface of the branch bundle of the optical fiber probe comes into contact with the irradiated skin site.
One of the branch lines of the fiber optic probe emits light from a white light LED to measure the reflected light spectrum, and the other branch line is an LED that emits light in the ultraviolet to blue light spectrum range. A suitable LED is selected by the switching device to emit light. Various wavelengths can be selected to select the optimal fluorescence excitation conditions, but the reflected light spectrum measurement is used to detect the autofluorescence generated by the effects of melanin and hemoglobin and to correct the measurement results Is done. The optical fibers in the optical fiber bundle are arranged in a certain order, and the optical fibers coming out from each of the three branch lines in the optical fiber bundle in which the optical fiber branch lines are collected are in a mosaic shape, and are sequentially arranged at intervals of 0.5 mm. Placed in.

  However, Patent Document 2 is configured such that light is irradiated to the lower arm of the subject via an optical fiber probe, and includes an optical fiber probe as a light transmission medium. However, there is a problem with such an optical fiber probe. Specifically, an optical fiber has a transmission loss for each specific wavelength due to its own medium characteristics. Further, in order to make light generated from a light source incident according to the total reflection condition of the optical fiber, further optical design and optical system are required. It was necessary.

  Furthermore, since the devices of Patent Documents 1 and 2 both use an optical fiber in a light receiving unit that receives light, there is a problem inherent to the optical fiber probe itself of the light receiving unit. By using the linear array detector, there is a disadvantage that the detection area for detecting the wavelength of the autofluorescence signal of the final glycation product by the linear array detector becomes relatively small. Therefore, the detected fluorescence signal is dispersed, and the light intensity of the wavelength to be detected using the linear array detector becomes relatively small. In addition, since an optical fiber probe, an optical fiber spectrometer, and the like are included, it is difficult to reduce the size of the equipment.

On the other hand, when measuring skin fluorescence for diagnosing disease, a reflected light detection method for detecting reflected light and skin fluorescence in a region where the light irradiated on the skin is reflected, and transmitted light for the light irradiated on the skin And a transmitted light detection method for detecting skin fluorescence at a position where the transmitted light is measured.
In this transmitted light detection method, in order to measure the intrinsic fluorescence intensity generated from the skin, the irradiation light must be transmitted to the target skin to be measured, and light must be detected on the skin on the opposite side of the target skin.

Usually, the target skin site to which the transmitted light detection method is applied is as follows. First, the earlobe has a thickness of about 3 mm and a large loss of transmitted light, and the influence of blood that absorbs light is very large. Fingers are greatly affected by the fluorescence generated in the nail when measured between the nail and the skin on the opposite side. On the other hand, when measuring the fluorescence between the right direction of the nail and the skin on the opposite side of the nail, the light path becomes long and the loss rate is large, and the skin condition of the finger and blood are greatly affected. However, when measuring the skin between the fingers, particularly the skin film between the thumb and the finger, there are the following advantages. First, the thickness is about 1 mm, and the loss of light is not large. Second, the influence of blood is small. Third, the effect of skin pigment is small, and fourth, measurement is simple.
On the other hand, even when selective diagnosis using transmitted light for some body parts is performed, the fluorescence intensity generated from the skin is generated not only in the fluorescent substance contained in the skin but also in the skin. Affected by light scattering and light absorption properties.

Therefore, an error due to measurement occurs due to the influence of such light scattering and light absorption properties. Therefore, in order to accurately detect skin fluorescence due to fluorescence excitation, such an error must be corrected. In particular, when diagnosing diseases such as diabetes from skin fluorescence measurements, this transmission is not significant because the difference in the number of subjects with and without the disease is not large enough to offset this error. When measuring skin fluorescence using a light detection method, a device capable of detecting a skin fluorescence signal more accurately is required.
When using a selective diagnostic apparatus using such a transmitted light detection method, it is necessary to solve the downsizing and mobility of the apparatus first, so that the efficiency of light irradiation and fluorescence detection within the apparatus is required. The
In addition, the efficiency of light irradiation and fluorescence detection is improved in order to more accurately distinguish between those who have the disease and those who are not, more accurately in the selective diagnostic site. On the other hand, it is very important to reduce measurement errors from the effects of light scattering and light absorption properties within the skin.

US Published Patent No. 2004-186363 US Published Patent No. 2008-103373

The present invention has been devised to solve the above problems. In the present invention, when the fluorescence of the final glycation product (AGE) is measured from the skin, the transmitted light with respect to the irradiation light, and in the skin Detects skin fluorescence detected together with the transmitted light out of the skin fluorescence due to scattering and absorption of the generated light, and calculates the corrected skin fluorescence signal from this, thereby detecting the skin fluorescence signal with improved accuracy Provided is a transmitted light detection type skin fluorescence measuring apparatus.
Further, in the present invention, a transmitted light detection type skin that can improve the possibility of diagnosis for diseases such as diabetes by accurately evaluating a diagnostic factor such as a final glycation product (AGE) from the corrected skin fluorescence calculation value. A fluorescence measuring device is provided.
Furthermore, the present invention provides a transmitted light detection type skin fluorescence measuring apparatus in which an optical system and a light source system are simply configured so that such a diagnostic process can be easily performed.

According to the present invention, it is constructed so as to allow the light irradiation and light detection with respect to reference sample or measured, in a transmission optical type measuring device for fluorescence of the skin,
A first light source that emits excitation light;
A second light source that emits light having a wavelength of skin fluorescence that is excited and emitted by the excitation light from the first light source;
The first light detector positioned to detect the transmitted light generated by the excitation light from the first light source, and said first skin fluorescence and the second light source generated by the excitation light from the light source a light source switching controller for controlling the second light detector positioned to detect the transmitted light generated by the light, said first and second light sources on / off from,
A calculation unit for calculating a skin fluorescence signal corrected by the fluorescence signal and the transmitted light signal detected by the first photodetector and the second photodetector,
Including
The light source switching control unit performs switching control of the first light source and the second light source so that lighting states of the first light source and the second light source are temporally separated.
A transmitted light detection type skin fluorescence measuring device is provided.

  In addition, the switching control unit continuously repeats the process of sequentially turning on and off the first light source and the second light source to generate a fluorescence signal and a transmitted light signal for the first light source and a transmitted light signal for the second light source, respectively. Provided is a transmitted light detection type skin fluorescence measurement device characterized by being configured to detect.

  Further, there is provided a transmitted light detection type skin fluorescence measurement apparatus, characterized in that a measurement object and a standard specimen are selectively positioned on the optical paths of the first light source and the second light source. .

  The first light source emits light of 370 nm ± 20 nm, and provides a transmitted light detection type skin fluorescence measuring apparatus.

  The second light source emits light of 440 nm ± 20 nm, and provides a transmitted light detection type skin fluorescence measurement apparatus.

  In addition, the switching control unit provides a transmitted light detection type skin fluorescence measurement apparatus that controls to turn off both the first light source and the second light source before turning on each light source.

  In addition, when the switching control unit turns off both the first light source and the second light source, the first photodetector and the second photodetector measure cancer signals, and the calculation unit measures the measured cancer signals. And a transmitted light detection type skin fluorescence measurement device characterized in that the fluorescence signal and the transmitted light signal detected from the stored cancer signal are compensated.

  Further, the switching control unit provides a transmitted light detection type skin fluorescence measurement device, wherein the first light source unit and the second light source unit are controlled to be repeatedly turned on and off at a cycle of 10 to 100 Hz.

  In addition, there is provided a transmitted light detection type skin fluorescence measurement apparatus further including a photodetector switching control unit for controlling on / off of the first photodetector and the second photodetector.

  Further, the optical sensor includes the first light source, the second light source, the first photodetector, and the second photodetector, and is configured to be electrically connectable to the optical sensor, and includes the arithmetic unit. Provided is a transmitted light detection type skin fluorescence measurement device characterized by being separated from a main body.

  The optical sensor includes a first fixing part connected to the first light source and the second light source, a first photodetector and a second fixing part connected to the second photodetector, and the first fixing. Provided is a transmitted light detection type skin fluorescence measurement device characterized in that the portion and the second fixing portion face each other and an insertion space is formed between them.

  The optical sensor includes a memory for storing detected information, and provides a transmitted light detection type skin fluorescence measurement apparatus.

  The optical sensor includes a common light source light guide for commonly transmitting light emitted from the first light source and the second light source, and provides a transmitted light detection type skin fluorescence measurement apparatus.

  In addition, the optical sensor includes a common detection light guide for commonly transmitting transmitted light and skin fluorescence to the first photodetector and the second photodetector. I will provide a.

  The optical sensor includes a first dichroic mirror disposed on an optical path so as to transmit each light emitted from the first light source and the second light source to the common light source light guide. A transmitted light detection type skin fluorescence measuring apparatus is provided.

  The optical sensor has a second dichroic mirror disposed on the optical path so as to separate the light transmitted from the common detection light guide and transmit the light to the first light detector and the second light detector. A transmitted light detection type skin fluorescence measurement device is provided.

  Further, between the first light source and the first dichroic mirror, the first wavelength light emitted from the first light source is allowed to pass, and the second wavelength light emitted from the second light source is suppressed. Provided is a transmitted light detection type skin fluorescence measuring apparatus characterized in that a filter is installed.

  In addition, an objective lens that focuses light emitted from the first light source and the second light source is installed between the first light source, the second light source, and the first dichroic mirror, respectively. A transmitted light detection type skin fluorescence measuring apparatus is provided.

  In addition, a first detection filter is provided between the second dichroic mirror and the first photodetector so as to pass light of the first wavelength and suppress light of the second wavelength, and the second dichroic mirror. And a second detection filter that suppresses light of the first wavelength and transmits light of the second wavelength is disposed between the second photodetector and the second photodetector. Providing equipment.

  In addition, between the first photodetector and the second photodetector and the second dichroic mirror, light that has passed through the second dichroic mirror is transmitted to the first photodetector and the second photodetector. Provided is a transmitted light detection type skin fluorescence measuring apparatus, in which an objective lens for focusing is respectively installed.

  In addition, the optical sensor includes a first light source light guide that transmits light emitted from the first light source and a second light source light guide that transmits light emitted from the second light source. Provided is a light detection type skin fluorescence measurement device.

  The optical sensor includes a first detection light guide that transmits transmitted light and skin fluorescence to the first photodetector, and a second detection light guide that transmits the second light detector to the second photodetector. Provided is a light detection type skin fluorescence measurement device.

  The first light source and the first light source light guide pass between the first wavelength light emitted from the first light source and suppress the second wavelength light emitted from the second light source. Provided is a transmitted light detection type skin fluorescence measuring apparatus characterized in that a filter is installed.

  In addition, a first detection filter is provided between the first light source light guide and the first photodetector to allow light of the first wavelength to pass and suppress light of the second wavelength, and the second light source. A transmitted light detection type skin characterized in that a second detection filter that suppresses light of the first wavelength and transmits light of the second wavelength is installed between the light guide and the second light detector. A fluorescence measuring device is provided.

  In addition, a first light source and a second light source are installed at the end of the first fixing unit, and the first light source and the second light source are configured to directly irradiate light to the measurement target. A first light detector and a second light detector are installed at the ends, and the first light detector and the second light detector are configured to directly detect transmitted light and skin fluorescence. A transmitted light detection type skin fluorescence measuring apparatus is provided.

  The first photodetector and the second photodetector are divided into a first wavelength (λ1) and a second wavelength (λ2) before the two sectors of the photodetector composed of two sectors. Provided is a transmitted light detection type skin fluorescence measurement device in which bandpass filters to be positioned are respectively located.

  In addition, the transmitted light detection type skin fluorescence measuring apparatus is provided, wherein the first fixing part and the second fixing part are manufactured in a clip shape so as to fix the measurement object in a pressurized state.

  In addition, a movable standard specimen is attached to the optical sensor, and the standard specimen is inserted when the object to be measured is removed from the insertion space between the first fixing part and the second fixing part. Provided is a transmitted light detection type skin fluorescence measurement device which moves so as to be positioned in a space.

  The optical sensor performs measurement on the skin when the skin to be measured is located in the insertion space, and performs measurement on the standard specimen when the measurement target is removed and the standard specimen is located in the insertion space. A transmitted light detection type skin fluorescence measuring device is provided.

  In addition, the optical sensor stores the measurement results for the skin to be measured and the standard specimen, transmits detection information for the stored skin and the standard specimen to the main body, and is corrected by the calculation unit. Provided is a transmitted light detection type skin fluorescence measuring apparatus configured to calculate a skin fluorescence value.

  The main body further includes a display unit, and the transmitted light detection type skin fluorescence measurement device is characterized in that the display unit outputs a corrected skin fluorescence signal calculated by the calculation unit.

  In addition, the calculation unit provides a transmitted light detection type skin fluorescence measuring apparatus, wherein the skin fluorescence value corrected by the following mathematical formula is calculated.

Formula: AF _corr = K [I (λ2, t1) / I ₀ (λ2, t1)] / {[T (λ1)] ^k1 [T (λ2)]} ^k2
(Where T (λ1) = I (λ1, t1) / I ₀ (λ1, t1): diffuse transmission coefficient at excitation wavelength T (λ2) = I (λ2, t2) / I ₀ (λ2, t2) : Diffuse transmission coefficient at emission wavelength I (λ2, t1): Inherent fluorescence (skin fluorescence) signal value of skin tissue I (λ1, t1): Transmitted light signal value of skin tissue at excitation light wavelength I (λ2, t2) ): Transmitted light signal value of skin tissue at synchrotron radiation wavelength k1, k2: Exponential coefficient of calibration function for excitation light and synchrotron radiation wavelength I ₀ (λ2, t1): Intrinsic fluorescence signal value at standard specimen I ₀ ( λ1, t1): Transmitted light signal value of the standard specimen at the excitation light wavelength I ₀ (λ2, t2): Transmitted light signal value of the standard specimen at the emitted light wavelength K: Characteristic of the standard specimen used Considered ratio factor)

  On the other hand, in the present invention, the light source unit that emits the excitation light, the light detection unit that is arranged to detect the transmitted light and the fluorescence signal with respect to the excitation light emitted from the light source unit, and the light source unit A pair of light transmission units configured to transmit excitation light to a measurement target and transmit the transmitted light and the fluorescence signal to a light detection unit, each light transmission unit being a light source unit or a light detection unit A mounting surface to which the measuring object is mounted, a reflecting surface that is extended from the mounting surface to the measuring object side and reflects light, and a contact surface that is coupled so that light is drawn into the measuring object. A transmitted light detection type skin fluorescence measuring apparatus is provided.

  The light source unit includes a first light source that irradiates excitation light and a second light source that irradiates light having a wavelength different from that of the first light source, and the light detection unit responds to a fluorescence signal and a reflected light signal. Provided is a transmitted light detection type skin fluorescence measurement apparatus characterized by including a first photodetector and a second photodetector that are installed so as to detect two different wavelengths.

  The transmitted light detection type skin fluorescence measuring apparatus is characterized in that the second light source irradiates light of a wavelength band of skin fluorescence excited and emitted by excitation light from the first light source.

  A light source switching control unit for controlling on / off of the first light source and the second light source; and a skin corrected from the fluorescence signal and the transmitted light signal detected from the first light detector and the second light detector. A transmitted light detection type skin fluorescence measuring apparatus comprising: a calculation unit that calculates a fluorescence signal.

  The transmitted light detection type skin fluorescence measurement device, wherein the pair of light transmission units are a first optical prism coupled to the light source unit and a second optical prism coupled to the light detection unit. I will provide a.

  The first optical prism and the second optical prism are triangular prisms having a triangular vertical cross-sectional shape, and provide a transmitted light detection type skin fluorescence measuring apparatus.

  In addition, a transmitted light detection type skin fluorescence measurement apparatus is provided, wherein a first light source is installed on a mounting surface of the first optical prism, and a second light source is installed on a reflection surface with respect to the first light source. To do.

  The transmitted light detection type skin is characterized in that a first photodetector is installed on a mounting surface of the second optical prism, and a second photodetector is installed on a reflection surface with respect to the first photodetector. A fluorescence measuring device is provided.

  The transmitted light detection type skin fluorescence measurement apparatus is characterized in that the pair of light transmission parts are a first light pipe connected to the light source part and a second light pipe connected to the light detection part. I will provide a.

  The transmitted light detection type skin characterized in that the first light pipe and the second light pipe have a tapered column shape having an inclined reflecting surface and a mounting surface having an area larger than the contact surface. A fluorescence measuring device is provided.

  In addition, a transmitted light detection type skin fluorescence measuring apparatus is provided, wherein a first light source and a second light source are installed on a mounting surface of the first light pipe.

  In addition, a transmitted light detection type skin fluorescence measurement apparatus is provided in which a first light detector and a second light detector are installed on a mounting surface of the second light pipe.

  Further, the present invention provides a transmitted light detection type skin fluorescence measurement apparatus, wherein a dichroic prism for separating the wavelength of light detected on the mounting surface side of the second light pipe into two bands is installed.

  The first photodetector may be installed to detect reflected light from the dichroic prism, and the second photodetector may be installed to detect transmitted light from the dichroic prism. A transmitted light detection type skin fluorescence measuring apparatus is provided.

  The first light pipe and the second light pipe are vertical light pipes extending perpendicularly to a contact surface with a measurement object, and provide a transmitted light detection type skin fluorescence measurement apparatus.

  The first light pipe and the second light pipe are horizontal light pipes that extend horizontally to a contact surface with a measurement object, and provide a transmitted light detection type skin fluorescence measurement device.

  The transmitted light detection type skin fluorescence measurement device is characterized in that the reflection surfaces of the first light pipe and the second light pipe are inclined reflection surfaces having a narrow cross-sectional area from the mounting surface to the contact surface side. provide.

  In addition, the transmitted light detection type skin fluorescence measurement device is provided in which the mounting surfaces of the first light pipe and the second light pipe are formed so as to be inclined to the reflection surface.

  In addition, the transmitted light detection type skin fluorescence measurement device is provided in which the reflection surfaces of the first light pipe and the second light pipe include a bent reflection surface inclined with respect to the contact surface.

  In addition, there is provided a transmitted light detection type skin fluorescence measuring apparatus, wherein the reflection surfaces of the first light pipe and the second light pipe are mirror-coated.

  The transmission further includes a transport unit for moving the light transmission unit up and down, a thickness indicator for measuring the distance between the two light transmission units and notifying the thickness of the object to be measured. Provided is a light detection type skin fluorescence measurement device.

  In addition, the transmitted light detection type skin fluorescence measurement device is further provided, wherein the contact surface of the light transmission unit further includes an optical connection unit that contacts the measurement target.

  In addition, the transmitted light detection type skin fluorescence measurement device is characterized in that the optical connection part constitutes a connection layer made of a liquid substance or an elastic material between the light transmission part and the measurement object.

  The transmitted light detection type skin fluorescence measuring apparatus according to the present invention has the following effects.

  First, the present invention is capable of easily diagnosing diabetic diseases by evaluating skin autofluorescence, enabling a large-scale examination to grasp potential diabetic patients, and for cardio-vascular and related complications. Risk can be predicted.

  Secondly, in the present invention, there is an effect of improving the light integration degree and the light homogeneity with respect to the light emitted from the light source and irradiating the measurement object with uniform light.

  Third, in the present invention, the light from the light source is efficiently accumulated and irradiated to the skin tissue, while the mirror reflection on the skin tissue surface is minimized to improve the light efficiency and reduce the size of the apparatus. Is possible.

  Fourthly, in the present invention, by adopting a method of measuring transmitted light at the time of measuring skin fluorescence, the cause of error due to mirror reflection on the skin surface is fundamentally removed, while the roughness of skin, scars, hair The influence of internal elements such as skin external elements and skin pigments and blood hemoglobin is minimized, thereby enabling accurate diagnosis of the disease.

  Fifth, in the present invention, errors due to scattering and absorption of light generated inside the skin can be easily corrected, so that accurate measurement of skin fluorescence can be performed, thereby enabling accurate diagnosis of diseases. .

  Sixth, the present invention can be manufactured in the form of a small scanner that includes a light source and a detection unit, and that can be grasped so that one end of the unit contacts the skin and measures skin fluorescence. Therefore, the measurement can be performed by a method in which the inspector scans the diagnostic region, so that real-time diagnosis can be performed by a non-invasive method.

FIG. 2 is a diagram illustrating light input from a light source and light detected by a photodetector for each time in order to explain a measurement principle of a transmitted light detection type skin fluorescence measurement apparatus according to the present invention. 1 is a diagram illustrating a schematic configuration of a transmitted light detection type skin fluorescence measurement apparatus according to the present invention. 6 is a schematic view illustrating a preferred light source and photodetector arrangement structure in the case where there is no space between the light source and the photodetector and the skin to be measured in the transmitted light detection type skin fluorescence measurement apparatus according to the present invention. 6 is a schematic view illustrating a preferred light source and photodetector arrangement structure in the case where a space exists between the light source and the photodetector and the skin to be measured in the transmitted light detection type skin fluorescence measurement apparatus according to the present invention. 3 is a view showing an example including an optical prism and an optical coupling part in the transmitted light detection type skin fluorescence measurement apparatus according to the present invention. FIG. 5 is a view showing another embodiment of the transmitted light detection type skin fluorescence measuring apparatus according to the present invention, which includes another embodiment including a light pipe and an optical connecting part. FIG. 5 is a view showing another embodiment of the transmitted light detection type skin fluorescence measuring apparatus according to the present invention, which includes another embodiment including a light pipe and an optical connecting part. FIG. 5 is a view showing another embodiment of the transmitted light detection type skin fluorescence measuring apparatus according to the present invention, which includes another embodiment including a light pipe and an optical connecting part. FIG. 5 is a view showing another embodiment of the transmitted light detection type skin fluorescence measuring apparatus according to the present invention, which includes another embodiment including a light pipe and an optical connecting part. FIG. 5 is a view showing another embodiment of the transmitted light detection type skin fluorescence measuring apparatus according to the present invention, which includes another embodiment including a light pipe and an optical connecting part. 4 is a view showing a preferred embodiment of a transmitted light detection type skin fluorescence measuring apparatus according to the present invention, which is another embodiment including a deformed light pipe and an optical connection part.

  The present invention relates to a skin fluorescence measuring apparatus for irradiating skin with excitation light for the purpose of diagnosis of diseases such as diabetes, and detecting skin fluorescence generated thereby, and in particular, inside the skin by irradiation light on the skin. Transmitted light detection type skin fluorescence measuring apparatus capable of accurately measuring the skin fluorescence information corrected from the transmitted light with respect to the irradiation light and the skin fluorescence information at the position where the transmitted light is detected among the scattered skin fluorescence. I will provide a.

  Therefore, in the present invention, information obtained from the measurement object in order to proceed with sequential measurement for the measurement object to be actually diagnosed and the standard specimen and remove individual deviations of the measurement object. Compared with the information obtained from the standard specimen, the on-off control of the light source and photodetector sequentially according to certain conditions required in the process can provide a corrected skin fluorescence value. A transmitted light detection type skin fluorescence measuring apparatus is provided.

  Hereinafter, a transmitted light detection type skin fluorescence measurement apparatus according to a preferred embodiment of the present invention will be described in detail with reference to the accompanying drawings.

  In order to measure the fluorescence generated in the skin, factors that affect the fluorescence measured along with the selection of the skin target must be considered. The measured fluorescence depends not only on the fluorescent substance contained in the skin, but also on the scattering and light absorption properties of light generated in the skin. In particular, it is necessary to correct the measured fluorescence value in consideration of the effects of light absorption and light scattering at the excitation light wavelength irradiated to excite the fluorescent material and the fluorescence wavelength generated by the fluorescent material. Therefore, in order to reduce the influence of optical elements that influence the fluorescence intensity, the following empirical formula can be considered.

AF _corr = AF / (T ₁ ^k1 T ₂ ^k2 ) ^−formula (1)

Fluorescence values AF measured to determine the corrected fluorescence value _{AF corr} were separated by diffuse transmission light value _{T 2} of the excitation diffuse transmission light value _{T 1} and the emitted light in the fluorescence wavelength band (emissioin). The two diffuse transmitted light values are adjusted by indices k1 and k2 having no order.

In the present invention, Equation (1) is used to obtain the skin fluorescence value corrected by the transmitted light detection method, and a specific value is introduced to obtain the corrected fluorescence value from an actual experiment.
I (λ2, t1): intrinsic fluorescence (skin fluorescence) signal value of skin tissue I (λ1, t1): transmitted light signal value of skin tissue at excitation light wavelength I (λ2, t2): skin at radiation wavelength Transmitted light signal value of tissue k1, k2: Exponential coefficient of calibration function for excitation light and emitted light wavelength K: Ratio coefficient considering characteristics of standard specimen used Relation to skin fluorescence value corrected by transmitted light detection method The formula is as follows.

AF _tissue = [I (λ2, t1)] / [I (λ1, t1) ^k1 I (λ2, t2) ^k2 ]; k1, k2 <1: −Expression (2)

Here, AF _tissue is a correction signal of intrinsic fluorescence of the skin tissue.

  The above-described light measurement is periodically repeated at different time intervals t1 and t2, and an average of the obtained measurement results is calculated in order to improve accuracy. Measurements are recorded in the form of a time diagram to track changes in a timely manner.

On the other hand, calibration for deviation depending on equipment and calibration measurement work for comparing results obtained from different specimens are necessary. Therefore, in the present invention, the same measurement was performed by measuring the skin target tissue and introducing a standard specimen. In order to increase the accuracy of measurement, the fluorescence intensity I ₀ (λ2, t1) of the standard specimen and the transmitted light signal values I ₀ (λ1, t1) and I ₀ (λ2) of the standard specimen with the excitation light and the emitted light T2) are preferably substantially the same as the optical characteristics of the skin.

The signal value generated during the measurement process of the introduced standard specimen is displayed in the same manner as the target skin tissue symbol as follows.
I ₀ (λ2, t1): Intrinsic fluorescence signal value at the standard specimen I ₀ (λ1, t1): Transmitted light signal value at the standard specimen at the excitation light wavelength I ₀ (λ2, t2): At the radiation wavelength The transmitted light signal value of the standard specimen of No. 2 The processing of the signal acquired by the standard specimen is calculated by the following formula (3) as in the formula (2).

AF _reference = [I ₀ (λ2, t1)] / [I ₀ (λ1, t1) ^k1 I ₀ (λ2, t2) ^k2 ] ^−Formula (3)

The normalized and final corrected intrinsic fluorescence values, which are the results of dividing the AF _tissue by AF _reference , are as follows.

AF _corr = K (AF _tissue / AF _reference ) _−formula (4)

AF _corr = K [I (λ2, t1) / I ₀ (λ2, t1)] / {[I (λ1, t1) / I ₀ (λ1, t1)] ^k1 [I (λ2, t2) / I ₀ ( [lambda] 2, t2)]} ^k2 -Equation (5)
(In the formula, K is a ratio coefficient considering the characteristics of the standard specimen used.)
The formula (5) is simply created again as follows.

AF _corr = K [I (λ2, t1) / I ₀ (λ2, t1)] / {[T (λ1)] ^k1 [T (λ2)]} ^k2 −Expression (6)
T (λ1) = I (λ1, t1) / I ₀ (λ1, t1): Diffuse transmission coefficient of excitation wavelength T (λ2) = I (λ2, t2) / I ₀ (λ2, t2): Diffusion of radiation wavelength Transmission coefficient

  Therefore, the transmitted light detection type skin fluorescence measuring apparatus according to the present invention calculates the skin fluorescence value corrected by the above-described calculation process.

  Furthermore, the principle proposed for the measurement is explained in detail as shown in FIG.

  FIG. 1 shows light input from a light source and light detected by a light detector for each time in order to explain the measurement principle of a transmitted light detection type skin fluorescence measurement device according to the present invention. As shown in FIG. 1, in the transmitted light detection type skin fluorescence measuring apparatus according to the present invention, a first condition for irradiating light corresponding to a wavelength band of excitation light (first wavelength, λ1) as an input and generated by the excitation light The measurement under the first condition and the second condition is continuously performed while the second condition for irradiating the light corresponding to the wavelength band of the skin fluorescence (second wavelength, λ2) is temporally separated. The wavelength band of the irradiation light corresponding to the first condition and the second condition is selectively configured according to the skin fluorescence to be detected. For example, as a preferred embodiment of the present invention, the skin fluorescence for AGE is detected. The first condition is light having a first wavelength of 370 nm ± 20 nm as excitation light for fluorescence excitation, and the second condition is light having a second wavelength of 440 nm ± 20 nm corresponding to the wavelength of skin fluorescence for AGE Can be used selectively.

  Specifically, a skin tissue (Tissue) corresponding to a measurement target in a diagnostic observation process using an optical sensor including a light source that emits light of two different wavelengths and a photodetector that detects light of two different wavelengths. ) Or a standard sample (Reference sample) and the optical sensor in contact with each other during the calibration process.

  In connection with the measurement process, FIG. 1A is an operating time diagram showing that each light source for two different wavelengths is operating in a time-separated manner. At this time, the light beam (λ1, t1) emitted from the first light source of the excitation light source is different from the light beam (λ2, t2) from the second light source of the standard light source in another wavelength band, and does not intersect. It is important to configure to exist in the time zone.

  FIG. 1B is an operation time diagram for two photodetectors. In the same time zone in which the light beam (λ1, t1) from the first light source is irradiated, two signals for the excited skin fluorescence and transmitted light are generated. That is, the two signals generated at the excitation light wavelength are the transmitted light signal I (λ1, t1) and the excited fluorescence signal I (λ2, t1).

  On the other hand, a single signal is simply formed in the time zone in which the light beam (λ2, t2) from the second light source is irradiated. That is, the signal generated by the second light source is detected only in the transmitted light signal I (λ2, t2) in the wavelength band of the irradiated light.

  Therefore, in the transmitted light detection type skin fluorescence measurement apparatus according to the present invention, as shown in FIG. 1, the light irradiation by the first light source and the light irradiation by the second light source are continuously irradiated to the measurement object while being temporally separated. Then, after collecting the signals detected from the photodetectors at the time of each light irradiation, the corrected skin fluorescence value is calculated by calculating this by the above formula.

  On the other hand, FIGS. 2 to 4 show the examples of the transmitted light detection type skin fluorescence measurement apparatus according to the preferred embodiment of the present invention, which are obtained by the measurement principle described above.

  As shown in FIGS. 2 to 4, the transmitted light detection type skin fluorescence measurement device according to the present invention is connected to the optical sensor for irradiating the skin with excitation light and the like, and detects the fluorescence of the skin. And a main body for analyzing information detected from the sensor and displaying the information.

  However, it is one of the preferred embodiments of the present invention to separate the optical sensor and the main body in this way, and may be manufactured in the form of a single sensor without forming a separate main body if necessary. Other configurations may be further connected.

  The transmitted light detection type skin fluorescence measuring apparatus according to the present invention includes a light source and a light detector so as to irradiate light to an object to be measured and detect skin fluorescence generated from the irradiated light. Composed.

  In particular, in the present invention, in order to correct the detected skin fluorescence value and provide an accurate skin fluorescence value, two light sources that emit light of different wavelengths and different wavelengths generated from the two irradiation lights. It includes two photodetectors for detecting transmitted light and skin fluorescence.

Specifically, the two light sources include a first light source that emits light corresponding to a wavelength band of excitation light (first wavelength, λ ₁ ), and a wavelength band of skin fluorescence generated by the excitation light (first wavelength). It is composed of a second light source that emits light corresponding to two wavelengths, λ ₂ ), and the two photodetectors are installed at positions for detecting transmitted light with respect to the first light source and the second light source.

Two such photodetectors include a first photodetector that detects transmitted light (λ ₁ ) with respect to excitation light from the first light source, skin fluorescence (λ ₂ ) generated by the excitation light, and a second light source. It is divided into the 2nd photodetector which detects the transmitted light ((lambda) ₂ ) with respect to the emitted light from.

  Therefore, the two light sources and the photodetector are arranged at positions where the transmitted light and the skin fluorescence can be detected at the same time, but preferably form a space in which an object to be measured or a standard specimen is inserted at the end of the optical sensor. Thus, the light source and the photodetector can be arranged to face each other.

  At this time, the light source and the light detector do not need to be directly opposed to each other. When the light source and the light detector are connected by an optical signal transmission unit such as a light guide, light detection is performed with a terminal portion where light irradiation is performed. It is sufficient that the end portions are arranged to face each other.

  Therefore, in the transmitted light detection type skin fluorescence measurement device according to the present invention, the light guide is disposed between the light source and the insertion space where the measurement target is located, so that the light guide guides the skin to be measured or the standard test from the light source. It can be configured such that light is transmitted to the strip. Further, by arranging a light guide between the insertion space and the light detector, the transmitted light and skin fluorescence transmitted through the skin are also transmitted to the light detector through the light guide. Can do.

  The optical sensor including the light source and the light detector is configured to be able to transmit light to the measurement object and detect an optical signal, and for this purpose, the end of the optical sensor contacts the skin or standard specimen of the measurement object. It can be constituted as follows.

  In the optical sensor, the first fixing part on the light source side irradiated with light from the light source and the second fixing part on the photodetector side for detecting the light are opposed to each other, and the scissors form an insertion space therebetween. Can be configured.

  Therefore, when the measurement object is located in the insertion space between the first fixing part and the second fixing part forming the scissors, light irradiation and light detection are performed on the measurement object.

  When there is no measurement object in the insertion space, a standard specimen can be inserted into the insertion space, and light irradiation and light detection are performed on the inserted standard specimen. The standard specimen may be configured to be automatically inserted into the insertion space, but in this case, if the measurement object is removed from the insertion space after the light irradiation and light detection are performed on the measurement object, It is preferable to configure so that the specimen is automatically inserted and light irradiation and light detection are performed on the standard specimen.

  At this time, as the standard specimen, one having optical characteristics of fluorescence and diffuse transmission substantially similar to the body tissue to be measured can be selected.

  On the other hand, the transmitted light detection type skin fluorescence measurement device according to the present invention may include a light source switching control unit for controlling on / off of the first light source and the second light source, and more preferably, the first light source. You may comprise so that the photodetector switching control part which controls ON / OFF of a photodetector and a 2nd photodetector may be included.

  Such a light source switching control unit and a photodetector switching control unit classify each light source and photodetector according to detection conditions of emitted skin fluorescence and transmitted light in order to accurately correct and calculate the skin fluorescence value. Then, switching control is performed so as to operate accurately.

Specifically, the light source switching control unit controls on / off of the light source, that is, turning on or off of the light source according to the light irradiation condition of the transmitted light detection type skin fluorescence measurement device. For example, excitation light (λ ₁ ) In the first condition for irradiating the measurement object, the second light source is turned off and the first light source is turned on, so that each light source is switching-controlled so that only the first light source emits light in the first wavelength band. On the other hand, under the second condition in which the measurement object is irradiated with radiation light (λ ₂ ) in a wavelength band different from that of the excitation light, the first light source is turned off and only the second light source emits light in the second wavelength band. The second light source can be turned on, and each light source can be controlled in this way.

  Similarly, the photodetector switching control unit is also configured to control on / off of the corresponding photodetector according to each measurement condition, and is a light for detecting light in a wavelength band to be detected under the current measurement condition. The detector is configured to be turned on / off.

  In particular, in the photodetector switching control unit, both the first condition for irradiating excitation light in the first wavelength band and the second condition for irradiating radiation light in the second wavelength band both detect optical signals for the second wavelength. Therefore, it is preferable that the second photodetector for detecting the light with respect to the second wavelength keeps the ON state continuously.

At this time, in the entire measurement process including the first condition and the second condition, the switching control for the light source is sequentially performed at a predetermined time. The switching cycle of each light source is diffused and transmitted by the blood flow in consideration of the pulse rate of the human body. It is preferable that the switching control is performed at a high frequency of 10 to 100 Hz level (about) so that the change in rate does not affect the measurement. In such a process, before each light irradiation and light detection is performed, after all the light sources are turned off, the dark signal level evaluation is performed to automatically compensate for light leaked from the outside. can do.

  In the transmitted light detection type skin fluorescence measurement apparatus according to the present invention, an optical filter can be selectively installed in front of the light source and the photodetector. Such an optical filter may be installed on the light path of the light source so that only light in a desired wavelength band is emitted by the light source, or only the light in the wavelength band to be detected by the photodetector It may be installed in front of the photodetector so as to enter the detector.

  On the other hand, the transmitted light detection type skin fluorescence measurement apparatus according to the present invention can be configured to include a main body configured to be connectable to an optical sensor including two light sources and two light detectors. The main body can be configured to include a calculation unit that calculates the magnitude of the skin fluorescence corrected from the information measured by the optical sensor.

  The main body can be configured to be connected to the optical sensor in a wired or wireless manner in order to receive information detected from the optical sensor, and by performing a calculation process as described above in the calculation unit of the main body. The corrected skin fluorescence value can be calculated.

  The main body may include a display unit to output information on the skin fluorescence signal, and the display unit is configured to output the corrected skin fluorescence signal calculated by the calculation unit to the outside. To do.

  Therefore, in the transmitted light detection type skin fluorescence measurement device according to the present invention having such a configuration, when the measurement target is located in the insertion space of the optical sensor, the optical sensor performs light irradiation and light detection processes on the measurement target, By inserting the standard specimen after the measurement object is removed, the light irradiation and light detection processes performed on the measurement object are similarly performed on the standard specimen.

  Information measured for the measurement target and the standard specimen is transmitted to the calculation unit of the main body, and the calculation unit corrects the skin fluorescence for the actual measurement target using information about the transmitted fluorescence signal and transmitted light signal. Calculate the value. The calculation result is displayed outside through a display unit formed on the main body.

  The measurement of the measurement object and the standard specimen is repeated at a constant cycle, and all the repeated measurement results are stored in the optical sensor using the memory, and the stored information is stored in the calculation unit for the calculation process in which correction is performed. Stored. At this time, the repeated measurement results are used for calculation by calculating an average value. Preferably, the measurement results can be stored in the form of a time diagram in order to track changes in the measurement results.

  FIG. 2 relates to a preferred embodiment of the transmitted light detection type skin fluorescence measurement apparatus according to the present invention, and is configured such that the first light source 111 and the second light source 112 transmit light to the measurement target side by a common light guide. On the other hand, a common light detector light guide is disposed on the opposite side of the common light source light guide, and the first light detector 121 and the second light detector are connected via the common detection light guide 128. It is an example including the optical sensor 100 configured to transmit transmitted light and skin fluorescence.

  As shown in FIG. 2, the light emitted from the first light source 111 and the second light source 112 enters the common light source light guide 117 through the lens. In this case, the light source may be an LED, a laser diode, or other light source that provides sufficient light brightness in the excitation and emission wavelength ranges. Between the first light source 111 and the common light source light guide 117, a light source filter 114 that suppresses light of the second wavelength (λ2) generated from the second light source 112 is installed. The second light source 112 may not be provided with a separate filter, and the second detection filter 125 is provided in front of the second photodetector 122. Therefore, the wavelength band of the light emitted from the second light source 112 can be wider than the wavelength band passing through the second detection filter 125, for example, a white light LED can be used as the second light source 112.

  Light generated from the first light source 111 and the second light source 112 enters the common light source light guide 117 via the first dichroic mirror 113. At this time, the objective lens 115 is interposed between the first dichroic mirror and each light source. , 116 can be installed. Further, under the condition that the second wavelength (λ2) is larger than the first wavelength (λ1), the first dichroic mirror 113 reflects the light of the first wavelength (λ1) of the short wavelength light and the first wavelength of the long wavelength light. Two wavelengths (λ2) of light are passed. Conversely, the first dichroic mirror 113 may be configured to pass a short wavelength and reflect a long wavelength. In this case, the positions of the first light source 111 and the second light source 112 must be changed. The power sources of the first light source 111 and the second light source 112 are switched and supplied by a light source switching controller, and preferably supplied by a relay switch in the driver module 134 as shown in FIG. The power supply to is alternately performed.

  When the measurement target (T) is located in the insertion space of the optical sensor 100, the optical sensor 100 performs light irradiation and light detection processes on the measurement target (T), and after the measurement target (T) is removed, the standard test is performed. By automatically inserting the piece (R), the light irradiation and light detection processes performed on the measurement object are performed on the standard specimen (R) in the same manner.

  Information measured for the measurement target (T) and the standard specimen (R) is transmitted to the calculation unit 210 of the main body 200, and the calculation unit 210 uses the transmitted information regarding the fluorescence signal and the transmitted light signal. The corrected skin fluorescence value for the actual measurement object is calculated. The calculation result is displayed outside through the display unit 220 formed on the main body 200.

  On the other hand, as shown in FIG. 2, the light that has entered through the common detection light guide 128 enters the first photodetector 121 and the second photodetector 122 through an optical system such as the objective lenses 126 and 127. The role of distributing light to the first photodetector 121 and the second photodetector 122 is performed by the second dichroic mirror 123. The second dichroic mirror 123 can be configured to reflect short wavelength light and allow long wavelength light to pass therethrough like the first dichroic mirror 113. Further, as in the case where the positions of the first light source 111 and the second light source 112 are changed by the first dichroic mirror 113, the positions of the first light detector 121 and the second light detector 122 are changed, and the corresponding wavelength passes. And the reflection characteristics can be changed to the opposite. At this time, the objective lenses 126 and 127 have a function of effectively collecting light in the photodetector.

  Each filter is installed in front of the photodetector. The first detection filter 124 installed in front of the first photodetector 121 is configured to pass the spectral component of the first wavelength (λ1) and suppress the spectral component of the second wavelength (λ2). On the other hand, the second detection filter 125 is configured to pass the spectral component of the second wavelength (λ2) and suppress the spectral component of the first wavelength (λ1).

  In addition, the transmitted light detection type skin fluorescence measurement apparatus according to the present invention controls the light irradiation from the light source in the optical sensor 100, processes the detected optical signal, and transmits it to the computing unit side (Electronic). control module (ECM) 130.

  The signals transmitted from the first photodetector 121 and the second photodetector 122 enter the analog-to-digital converters 131 and 132 belonging to the electronic control module 130, and then the data transfer module (DTM) 133. It can be configured to be transmitted to the arithmetic unit 210 of the main body through a bidirectional bus. Here, the data transmission module 133 selects data by acting as a multiplexer by time-division control transmission of a digital signal. The synchronization function between the data transmission module and the relay switch is executed from the main body by a bidirectional bus.

  The main body 200 may be configured to control the driver module 134 corresponding to the light source switching control unit, and to control the entrance / exit module of the standard specimen (R) by the measurement insertion unit. In the main body, statistical processing of the signal is performed, the corrected fluorescence value is calculated by the above-described mathematical formula, and work related to signal processing, control, data input, and the like can be performed. Can be configured to output.

  Furthermore, in a preferred embodiment of the present invention, in order to detect skin fluorescence against AGE, light having a first wavelength of 370 nm ± 20 nm can be used as excitation light for fluorescence excitation, and the skin against AGE is used as emitted light. Light having a second wavelength of 440 nm ± 20 nm corresponding to the wavelength of fluorescence can be used.

  In this case, the first light source 111 is a light emitting diode that emits light in a first wavelength band of 370 nm ± 20 nm, and the second light source 112 is a light emitting diode that emits light in a second wavelength band of 440 nm ± 20 nm. Can be configured. The first photodetector 121 may be a photodiode that detects light in the first wavelength band, and the second photodetector 122 may be a photodiode that detects light in the second wavelength band. it can.

  FIG. 3 is a view showing another embodiment of the transmitted light detection type skin fluorescence measuring apparatus according to the present invention, in which a pair of light guides are individually installed on the light source side and the photodetector side, respectively. Concerning structure.

  Specifically, in the transmitted light detection type skin fluorescence measuring apparatus shown in FIG. 3, as shown in FIG. 2, the first light source, the second light source, the first light detector, the second light detector, and the electronic control module are provided. Unlike the embodiment of FIG. 2, the light guide is configured so that individual light guides are connected to the respective light sources and light detectors to perform light transmission, unlike the embodiment of FIG.

  Therefore, in the embodiment of FIG. 3, the first light source light guide 314 and the second light source light guide 315 are connected to the first light source 311 and the second light source 312 respectively, and the first detection light guide 325 and the second light source 312 are on the opposite side. Two detection light guides 326 are connected to the first light detector 321 and the second light detector 322, respectively.

  That is, light transmission for light irradiation and light detection is performed through each light guide, but in this embodiment, a dichroic mirror for collecting or dispersing light as shown in FIG. 2 is unnecessary.

  In the example of FIG. 3, the light guide can be directly coupled to the light source or the light detector without transmitting light through an optical system such as a dichroic mirror, so that the objective lens for focusing the light is used. Such a configuration is unnecessary.

  In addition, the light source filter 313, the first and second detection filters 323 and 324, the analog-digital converters 331 and 332, the data transmission module 333, and the main body 400 including the calculation unit 410 and the display unit 420 connected thereto. Is as described in FIG.

  On the other hand, as another embodiment of the transmitted light detection type skin fluorescence measurement apparatus according to the present invention, in FIG. The example comprised in this way is shown.

  In the embodiment of FIG. 4, the first light source 511 and the second light source 512 located on the same chip generate light of the first wavelength (λ1) and the second wavelength (λ2), respectively. If the spectral component of the second wavelength (λ2) is not included, no filter is necessary.

  In the embodiment of FIG. 4, the photodetector is composed of two sectors, but a band-pass filter that separates the first wavelength (λ1) and the second wavelength (λ2) is positioned in front of the two sectors. A first photodetector 521 and a second photodetector 522 are configured. The electronic control module sequentially turns on and off the first light source 511 and the second light source 512, and controls and synchronizes the light detection signals input from the two channels from the photodetector by a time division method. Turn into.

  In the embodiment of FIG. 4, the light source and the photodetector are positioned corresponding to each other, so that the light source side end portion and the light detector side end portion form a clip to measure the object to be measured. It can be fixed under pressure. In this case, after the measurement target is sandwiched between the clip-shaped light source sensors, the light irradiation and light detection processes are performed on the measurement target.After the measurement target is removed, the standard specimen is automatically sandwiched between the clips and automatically measured. The same process as the light irradiation and light detection process performed on the standard specimen is performed.

  Then, after converting into a corresponding digital signal, the information regarding the measured optical signal is transmitted to the fixed main body 600 using a communication module, and the arithmetic unit 610 of the main body transmits the transmitted fluorescence signal and the transmission signal. The corrected skin fluorescence value for the actual measurement object is calculated using the information relating to the optical signal. The calculation result is displayed outside through a display unit 620 formed on the main body 600.

  Furthermore, the present invention is characterized in that a light transmission part having a new structure such as an optical prism or a light pipe is included in the light path so as to improve light transmission and light detection efficiency.

  A light transmission unit including such an optical prism or a light pipe irradiates concentrated light uniformly on a narrow region of the skin site to be measured, and collects the transmitted light on the light detection unit side. Function.

  Specifically, the light transmission unit included in the optical sensor according to the present invention is configured so that a part of the drawn light is reflected inside, so that the light that is not irradiated to the region to be measured is not lost, and the measurement region Or it has the structure which can be transmitted to the photon detection part side. Accordingly, the light transmission unit according to the present invention has at least one reflection surface in addition to the mounting surface on which the light source or the photodetector is positioned and the mounting surface so that the internal reflection of the light drawn into the inside is possible. It has the structure containing. Moreover, the light transmission part by this invention contains the contact surface which contacts a measuring object other than the mounting surface and reflection surface of light.

  The light transmitting unit including the light mounting surface, the reflecting surface, and the contact surface in this manner can be an optical prism or a light pipe, which will be described in detail below. This is shown in detail in FIG.

  FIG. 5 is a view showing a preferred embodiment of the transmitted light detection type skin fluorescence measuring apparatus according to the present invention, and shows an example using an optical prism.

  First, since an LED light source that is often used as a general excitation light source is irradiated with light with a wide divergence angle, a loss of light irradiated to an area to be measured occurs, and the light irradiated skin is thereby caused. There is also a loss in the amount of light that is detected by the photodetector with the fluorescence scattered from the region.

  Since the detected skin fluorescence is significantly smaller than other excitation light and its reflected light, even if such light loss is a minute amount, the accuracy of the measurement and the reliability of diagnosis are greatly reduced. It becomes a factor to make.

  On the other hand, the present invention proposes a transmitted light detection type skin fluorescence measuring apparatus including optical prisms 720 and 730 as a light transmitting portion as shown in FIG. 5 in order to prevent such light loss.

  In the present invention, the excitation light irradiated from the light source unit is condensed using an optical prism, and the light homogeneity at the skin site to be measured is improved. Further, the transmitted light and the fluorescence transmitted through the measurement target site are transmitted to the light detection unit side via another optical prism.

  Referring to FIG. 5, in the transmitted light detection type skin fluorescence measurement apparatus according to the present embodiment, optical prisms 720 and 730 are installed on the light source unit side and the light detection unit side, respectively. In order to distinguish the two optical prisms 720 and 730, the optical prism adjacent to the light sources 711 and 712 is referred to as a first optical prism 720, and the optical prism adjacent to the photodetectors 741 and 742 is second. This is an optical prism 730.

  The first optical prism 720 reflects a part of light that has not been transmitted to the measurement target side among the mounting surface on which the light source is installed and the light incident through the mounting surface with respect to the light source unit. Including reflective surfaces.

  That is, referring to FIG. 5, when the first light source 711 is used as a reference, the optical prism surface on which the first light source 711 is installed is a mounting surface 721, and is irradiated from the first light source 711 adjacent to the mounting surface 721. An optical prism surface that can reflect the reflected light is a reflection surface 722.

  In addition, when the second light source 712 is used as a reference in FIG. 5, the optical prism surface serving as the reflective surface 722 of the first light source 711 becomes the mounting surface 722 of the second light source 712, and the mounting surface 721 of the first light source 711 is the reflective surface. 721.

  In the embodiment including a large number of light sources, the mounting surface and the reflection surface are relative concepts based on any one of the light sources. In the transmitted light detection type skin fluorescence measurement apparatus according to the present invention, What is necessary is just to include such a mounting surface and a reflective surface with reference to the light source. Therefore, in the present invention, the light emitted from the light source unit is totally reflected inside and concentrated on the skin side as much as possible, and the light thus collected causes the inhomogeneity of the light source, that is, the optical axis. The characteristic that the light intensity decreases as going outward from the center is reduced, and an improved light homogeneity can be obtained.

  At this time, a filter may be installed on the mounting surface (or reflecting surface) of the optical prism so as to transmit only light in a specific wavelength band.

  Further, the first optical prism 720 further includes a contact surface 723 that contacts and pressurizes the measurement site at the time of measurement in contact with or close to the measurement target (T) in addition to the mounting surface and the reflection surface. Such a contact surface 723 is a surface connected to the measurement site by the first optical prism 720, and light is transmitted to the measurement site via the contact surface 723.

  On the other hand, the light that has passed through the contact surface 723 of the first optical prism 720 generates fluorescence in the skin, and is emitted to the photodetectors 741 and 742 side together with the transmitted light. Therefore, as shown in FIG. 5, in the preferred embodiment of the present invention, the second optical prism is used as another light transmission unit for efficiently transmitting the transmitted light and fluorescence sent to the photodetectors 741 and 742 side. 730 is further included.

  The second optical prism 730 is similar to the first optical prism 720 described above, for example, the mounting surface 731 on which the photodetector is mounted on the basis of the first photodetector 741, and the transmission surface adjacent to the mounting surface. It is configured to include a reflecting surface 732 that is an optical prism surface capable of reflecting light and fluorescence, and a contact surface 733 that contacts or presses against a measurement site.

  Specifically, in the second optical prism 730 having the above-described configuration, transmitted light and fluorescence transmitted through the skin site of the measurement target (T) enter the photodetector side or are detected by the photodetectors 741 and 742 by internal reflection. Configured to enter the side.

  Furthermore, in the transmitted light detection type skin fluorescence measuring apparatus according to the present invention, the transmitted light and fluorescence of the skin part of the measurement target (T) are refracted and scattered by the light on the contact surface with the skin part on the detector side. An optical coupling part 750 for preventing leakage light generated between the two may be provided.

  The optical coupling unit 750 is configured to be positioned between the contact surface of the optical prism adjacent to the skin of the measurement target (T) and the skin surface, and the optical coupling unit is formed of the optical prism. Contact with the contact surface and the skin surface, respectively.

  Preferably, the optical coupling part is formed on a contact surface of the first optical prism 720, and contacts the contact surface and the skin surface to match the refractive index at the boundary and to make an optically smooth contact. Configure the layers.

  In detail, the optical connection 750 may prevent leakage light between the two media to prevent leakage light generated between the two media due to refraction and scattering of excitation light between the contacting optical prism and the skin tissue. While adjusting the refractive index between them, it plays a role in filling non-smooth parts such as fine irregularities of the skin tissue.

  The optical coupling portion in the present invention is made of a liquid material such as water or oil-immersed oil or an elastic material, and is selected from materials substantially similar to the refractive index of the optical prism and the skin.

  By such an optical coupling part, total internal reflection of irradiation light does not occur in the prism at the boundary between the prism and the skin tissue, and the efficiency with which the light emitted from the light source is input to the skin tissue is large. Improved.

  Therefore, the transmitted light detection type skin fluorescence measurement apparatus using such an optical prism and an optical coupling part improves the light integration degree and the light homogeneity, while the component of the transmitted light and the fluorescence that is mirror-reflected on the contact surface. It can be greatly reduced.

  Further, in the transmitted light detection type skin fluorescence measurement apparatus according to the present embodiment, as shown in FIG. 5, together with the two light sources 711 and 712 and the two photodetectors 741 and 742, a light source for controlling on / off of the two light sources. A switching control unit (not shown) and a calculation unit (not shown) that calculates a fluorescence signal detected from the two photodetectors and a skin fluorescence signal corrected from the transmitted light signal can be included. .

  In this case, as shown in FIG. 5, each of the first optical prism 720 and the second optical prism 730 is composed of a triangular prism-shaped optical prism having a contact surface adjacent to the skin side and two mounting surfaces (or reflection surfaces). can do.

  In addition, a light source and a photodetector are installed on the mounting surface of the optical prism. For example, as shown in FIG. 5, two light sources 711 and 712 are installed on the two mounting surfaces of the first optical prism 720, and two photodetectors 741 and 742 are mounted on the two mounting surfaces of the second optical prism 730. Is installed. At this time, filters 761 and 762 for removing noise and allowing only the wavelength band to be detected to pass are installed on the mounting surface of the second optical prism 730.

  Structural parts such as the mounting position of the light source and the light detector and the form of the optical prism may be appropriately modified as necessary. For example, a rectangular prism having a trapezoidal vertical cross section may be used as the optical prism, and the light source and the light detector may be appropriately disposed on the mounting surface instead of the contact surface.

  Furthermore, as described in FIG. 2 and the like described above, the transmitted light detection type skin fluorescence measurement device according to the present embodiment is the same except that light irradiation is performed by an optical prism placed between the measurement object. A corrected skin fluorescence value is obtained by the calculation process.

  6 and 7 show still another embodiment of the transmitted light detection type skin fluorescence measuring apparatus according to the present invention, and FIGS. 6 and 7 show an example in which a light pipe is used as a light transmission section.

  Referring to FIG. 6, in the embodiment using the light pipe, two optical prisms are used as a light transmission unit that transmits light from the light source unit, transmitted light that has passed through the skin, and secondary light of fluorescence to the light detection unit. Instead, two light pipes 820 and 830 are used.

  The light pipe in the present embodiment is made of glass like the optical prism, and can be constituted by a polygonal column or a cylinder having an inclined form in which the side surface becomes narrower as shown in FIG. Each light pipe has a structure including two surfaces at both ends formed along an inclined side surface, and a light source unit or a light detection unit is located on a wide surface of the two surfaces, and a narrow surface is formed. Is configured to contact the skin tissue to be measured. Therefore, the light pipe in the present embodiment is in the form of a tapered column having inclined side surfaces. At this time, the first light pipe 820 on the light source unit side and the second light pipe 830 on the light detection unit side are installed symmetrically with each other across the skin as shown in FIG.

  Therefore, the light pipe in this embodiment is connected to the mounting surfaces 821 and 831 on which the light sources 811 and 812 or the photodetectors 841 and 842 are installed, and the skin surfaces to be measured are connected to the mounting surfaces 821 and 831. The reflecting surfaces 822 and 832 are inclined surfaces extending in the direction of positioning, and the contact surfaces 823 and 833 that are connected to the reflecting surfaces 822 and 832 and come into contact with the skin tissue.

  In the transmitted light detection type skin fluorescence measuring apparatus having such a light pipe, the light irradiated from the light source part is reflected along the inclined reflecting surface 822 and moves to the measurement target (T) side, and the skin It enters the skin tissue through the contact surfaces 823 and 833 of the light pipe that come into contact with the tissue.

  In this embodiment, since a light pipe having a cross-sectional area that decreases from the mounting surface to the contact surface with respect to the light source unit is used, the light energy density emitted from the light source is concentrated in the contact area with the skin. Can be increased.

  Therefore, such a light pipe can collect light in a narrow area even in the case of an LED light source having a wide divergence angle, and even if it includes a plurality of light sources irradiated with different optical axes, the light passes through the light pipe and is uniform. Thus, the optical axis of the light applied to the skin can be matched.

  Furthermore, according to the present embodiment using a light pipe, the optical axis of the light source unit and the optical axis of the photodetector can be matched, so that the detection accuracy is improved.

  In this embodiment, since light is reflected and transmitted by the inclined reflecting surface, the uniform numerical light is irradiated over a wider range by increasing the numerical aperture (NA) at the site in contact with the skin. Therefore, the generation of secondary light can be increased.

  On the other hand, a second light pipe 830 is installed on the opposite side of the first light pipe 820 on the light source unit side, and transmitted light and fluorescence passing through the second light pipe 830 are installed on the mounting surface of the second light pipe 830. Will come to be detected. That is, among the light transmitted to the skin along the reflective surface of the first light pipe 820, transmitted light and fluorescence are emitted to the opposite skin, and these lights are transmitted along the reflective surface 832 of the second light pipe 830. It is transmitted to the detection unit side.

  The optical signal detected by the light detection unit is transmitted to the main body 860 including the calculation unit. As described above, the main body 860 uses the information on the transmitted fluorescence signal and the transmitted light signal to the actual measurement target. A corrected skin fluorescence value is calculated.

  In another embodiment of the invention, it may be considered to use an optical fiber instead of a light pipe. Specifically, an optical fiber may be used in place of the second light pipe, but the optical fiber is configured to be connected to an optical spectrometer. In this case, the optical fiber can be arranged opposite to the first light pipe, and the optical spectrometer is arranged to detect transmitted light and fluorescence that have passed through the optical fiber.

  On the other hand, FIG. 7 shows a modified example of the transmitted light detection type skin fluorescence measuring apparatus shown in FIG. 6, and shows an example in which a dichroic prism is installed on the photodetector side.

  Specifically, as shown in FIG. 7, a dichroic prism 870 can be installed near the mounting surface of the second light pipe 830 at a position before the light reaches the light detection unit. Such a dichroic prism 870 separates the secondary light generated in the skin tissue into two wavelength bands (λ1, λ2).

  The light separated into the two wavelength bands is detected by the photodetectors 841 and 842, but the light for each wavelength band is accurately detected so that the light reflected by the dichroic prism 870 or transmitted through the dichroic prism 870 can be accurately detected. The detectors can be installed on different surfaces of the light pipe. Therefore, the numerical aperture of the light reduced compared with the case where it is drawn into the skin tissue is improved by the two photodetectors 841 and 842 installed on two different surfaces in this way.

  Further, as described above, the first light pipe 820 and the second light pipe 830 align the optical axis to reduce the measurement error despite the spatial mismatch between the light source unit and the light detection unit. be able to.

  Further, in this embodiment, similarly to the embodiment including the optical prism described above, an optical coupling portion 850 is included between the skin portion of the measurement target (T) and the contact surface of the first light pipe 820. Can be configured. Such an optical connection unit 850 may be installed not only in the first light pipe 820 but also in the second light pipe 830, and the matters regarding the optical connection unit 850 are as described above.

  8 to 10 show actual examples of the transmitted light detection type skin fluorescence measuring apparatus manufactured as shown in FIG. 6, and show an optical sensor having a main configuration. In the embodiment manufactured as described above, as an optical sensor including a light source, a light detector, and two light pipes, a transport part that transports the light pipe up and down at the time of measurement of transmitted fluorescence, and a light pipe by the transport part. A thickness indicator that informs the changing skin thickness by being raised and lowered is included. In addition, such an optical sensor is configured to be connected to a main body for controlling the light source and the photodetector and collecting measurement data.

  As shown in FIG. 8, a space for inserting the measurement target (T) is formed between the first light pipe 820 and the second light pipe 830, and the light source unit is different as shown in FIG. Two light sources 811 and 812 that emit light in the wavelength band are installed.

  A specific measurement process by the transmitted light detection type skin fluorescence measuring apparatus including such a configuration is as follows.

  After inserting an interstitial hole of a skin site to be measured into the optical sensor 800 and descending the first light pipe 820 downward, light is emitted from a light source.

  At this time, it is shown in FIG. 10 that the mixed light is irradiated from the two light sources through the first light pipe 820, and in particular, as shown in the enlarged view on the right side, Distribution characteristics can be confirmed. That is, as can be seen from such light distribution characteristics, it can be confirmed that the mixed light has a uniform distribution and is focused on the measurement target (T) side.

  Light focused on the region to be measured, that is, transmitted light that passes through the skin and skin fluorescence due to fluorescence excitation, are detected by the photodetector through the second light pipe 830.

  At this time, in order to improve the reliability of the measurement, an operation for maintaining the thickness of the skin site to be measured constant is performed. Therefore, in this invention, the conveyance part (not shown) for conveying the 1st light pipe and pressurizing the skin site | part of a measuring object (T) is included. In addition, a thickness indicator (not shown) for measuring the skin thickness in a state where the first and second light pipes are transported and the skin part is pressurized by the transport unit is configured to be included. Can do.

  Accordingly, in the measurement process, the transport unit transports the first light pipe 820 to pressurize the skin region, and then uses the thickness indicator to transport the first light pipe 820 and the second light pipe 830. The thickness of the object to be measured (T) is confirmed by measuring the distance between the two, and when the pressure is increased by a predetermined thickness, the conveyance of the conveyance unit is stopped.

  Through such a process, the thickness of the object to be measured can be kept constant, and a constant repeatability can be obtained.

  On the other hand, FIG. 11 shows another embodiment of the present invention, which includes a modified light pipe.

  FIG. 6 shows an example of a vertical light pipe extended in a direction perpendicular to the contact surface with the measurement object, and FIG. 11 shows an example of a horizontal light pipe extended in a direction substantially parallel to the measurement object. .

  Specifically, the embodiment of FIG. 11 also includes a light source and a light detector, and a horizontal light pipe is used as a light transmission unit for transmitting light from the light source unit including the light source to the light detection unit including the light detector. Including. Such a horizontal light pipe is composed of two first and second light pipes 920 and 930 that are in contact with the top and bottom of the measurement target (T), and each of the light pipes is a light source 911 or 912 or a light detector 941. , 942 are mounted on the mounting surfaces 921, 931, the light irradiated from the light source or the reflection surfaces 922, 932 for reflecting and transmitting the transmitted light and the fluorescence transmitted through the skin, and the measurement object (T) in contact with each other. Contact surfaces 923, 933.

  In the present embodiment, the first light pipe 920 is mounted with a light source unit in order to effectively make uniform light incident on the contact surface 923 with the measurement target (T) positioned so as to be substantially parallel to the reflection surface 922. A surface 921 is formed to be inclined to the reflection surface 922. Therefore, the irradiation light from the light source unit installed on the mounting surface 921 is reflected along the reflection surface 922 and drawn to the measurement target (T) side through the contact surface 923. Similarly, the mounting surface 931 on the light detection unit side is also formed to be inclined to the reflection surface 932 of the second light pipe.

  Further, the first light pipe 920 and the second light pipe 930 are configured to include bent reflection surfaces 924 and 934 inclined with respect to the contact surface as shown in FIG. 11 on the contact surfaces 923 and 933 side. Thus, the irradiation light can be effectively drawn into the measurement target side, and the transmitted light and the fluorescence can be effectively transmitted to the photodetector side.

  The light pipe in this embodiment is mirror-coated on the reflective surface by a separate vapor deposition process so that the light is reflected by the reflective surface of the side surface, so that light is transmitted to the skin side on the contact surface of the light pipe. Avoid mirror coating. Therefore, light irradiation and secondary light collection are performed by the contact surface that is not mirror-coated. Further, the mounting surface on which the light source unit and the light detection unit are located is also configured not to be mirror-coated.

  Further, as in the above-described embodiment, an optical coupling portion 950 is inserted between the contact surfaces 923, 933 of the light pipe and the measurement target (T), and the optical transmission portion 950 transmits light. Efficiency can be improved. Moreover, the conveyance part and thickness indicator for pressurizing a measuring object and maintaining the thickness may be included similarly to the example of FIG.

  Therefore, in the embodiment using the horizontal light pipe as shown in FIG. 11, the optical sensor can be simply configured like a clip, so that the measurement can be simplified.

  Although the present invention has been described with reference to preferred embodiments, those skilled in the art can understand that modifications and changes can be made to the elements of the present invention without departing from the scope of the present invention. it can. Further, special circumstances and materials can be changed within a range not departing from the essential area of the present invention. Accordingly, the invention is not limited by the detailed description of the preferred embodiments of the invention, but includes any embodiment within the scope of the appended claims.

100 optical sensor 200 main body 111 first light source 112 second light source 113 first dichroic mirror 114 light source filters 115 and 116 objective lens 117 common light source light guide 121 first light detector 122 second light detector 123 second dichroic mirror 124 second 1 detection filter 125 2nd detection filter 126, 127 objective lens 128 common detection light guide 130 electronic control module 131, 132 analog-digital converter 133 data transmission module 134 driver module 210 arithmetic unit 220 display unit 300 optical sensor 400 main body 311 first 1 light source 312 second light source 313 light source filter 314 first light source light guide 315 second light source light guide 321 first light detector 322 second light detector 323 first detection filter 324 second detection filter 25 First detection light guide 326 Second detection light guide 330 Electronic control modules 331 and 332 Analog-digital converter 333 Data transmission module 334 Driver module 410 Calculation unit 420 Display unit 511 First light source 512 Second light source 521 First light detection Unit 522 second light detector 530 electronic control module 531, 532 analog-digital converter 533 data transmission module 534 driver module 600 main body 610 arithmetic unit 620 display unit 711 first light source 712 second light source 720 first optical prism 730 second Optical prism 741 First light detector 742 Second light detector 750 Optical coupling unit 761,762 Filter 800 Optical sensor 811 First light source 812 Second light source 820 First light pipe 830 Second light pipe 841 First light Detector 842 Second light detector 850 Optical coupling portion 860 Main body 870 Dichroic prism 911 First light source 912 Second light source 920 First light pipe 930 Second light pipe 941 First light detector 942 Second light detector 950 Optical Connection part T Measurement target (skin)
R standard specimen

Claims (52)

And it is configured so as to allow the light irradiation and light detection with respect to reference sample or measured, in a transmission optical type measuring device for fluorescence of the skin,
A first light source that emits excitation light;
A second light source that emits light having a wavelength of skin fluorescence that is excited and emitted by the excitation light from the first light source;
The first light detector positioned to detect the transmitted light generated by the excitation light from the first light source, and said first skin fluorescence and the second light source generated by the excitation light from the light source a light source switching controller for controlling the second light detector positioned to detect the transmitted light generated by the light, said first and second light sources on / off from,
A calculation unit for calculating a skin fluorescence signal corrected by the fluorescence signal and the transmitted light signal detected by the first photodetector and the second photodetector,
Including
The light source switching control unit performs switching control of the first light source and the second light source so that lighting states of the first light source and the second light source are temporally separated.
It is characterized by
Transmitted light detection type skin fluorescence measurement device. The transmitted light detection type measurement apparatus, the first light source and the excitation light emitted from the second light source is transmitted to the measurement target, the transmitted light and the fluorescent signal the first optical detector and the second Including a pair of light transmitters configured to transmit to two photodetectors;
Each light transmission part
A mounting surface on which the first and second light sources or the first and second light detection units are mounted;
A reflecting surface for reflecting the light is extended to the measurement object side from the mounting surface,
A contact surface which is connected to the light is drawn into the measurement object,
Including,
The transmitted light detection type skin fluorescence measuring apparatus according to claim 1. The pair of light transmission units includes a first optical prism coupled to the first light source and the second light source, and a second optical prism coupled to the first photodetector and the second photodetector. It is characterized by
The transmitted light detection type skin fluorescence measuring apparatus according to claim 2. It said first optical prism and said second optical prism is characterized in that it is a triangular prism having a vertical cross-section of triangular,
The transmitted light detection type skin fluorescence measuring apparatus according to claim 3. Wherein the first light source is installed in the mounting surface of the first optical prism, the reflective surface with respect to the first light source and said second light source is disposed,
The transmitted light detection type skin fluorescence measuring apparatus according to claim 4. Wherein the mounting surface of the second optical prism the first photodetector is installed, the reflective surface relative to the first photodetector and said second photodetector are installed,
The transmitted light detection type skin fluorescence measuring apparatus according to claim 5. The pair of light transmission units may be a first light pipe coupled to the first and second light source units and a second light pipe coupled to the first and second light detection units. To
The transmitted light detection type skin fluorescence measuring apparatus according to claim 2. Said first light pipe and the second light pipe has an inclined reflective surface, wherein said mounting surface is a tapered pillar shape having an area larger than the contact surface,
The transmitted light detection type skin fluorescence measuring apparatus according to claim 7. The mounting surface of the first light pipe, wherein the first and second light sources are installed,
The transmitted light detection type skin fluorescence measuring apparatus according to claim 7. The mounting surface of the second light pipe and said first photodetector and said second photodetector are installed,
The transmitted light detection type skin fluorescence measuring apparatus according to claim 7. A dichroic prism for separating the wavelength of light detected on the mounting surface side of the second light pipe into two bands is installed,
The transmitted light detection type skin fluorescence measuring apparatus according to claim 7. The first photodetector is installed to detect reflected light from the dichroic prism, and the second photodetector is installed to detect transmitted light from the dichroic prism.
The transmitted light detection type skin fluorescence measuring apparatus according to claim 11. It said first light pipe and the second light pipe, characterized in that it is a vertical light pipes extend perpendicularly to said contact surface with the measurement object,
The transmitted light detection type skin fluorescence measuring apparatus according to claim 7. It said first light pipe and the second light pipe, characterized in that it is a horizontal type light pipe is extended horizontally to the contact surface between the measurement object,
The transmitted light detection type skin fluorescence measuring apparatus according to claim 7. The reflecting surface of the first light pipe and the second light pipe, wherein said a reflecting surface inclined in cross-sectional area narrows in the contact surface side from the mounting surface,
The transmitted light detection type skin fluorescence measuring apparatus according to claim 14. Mounting surface of the first light pipe and the second light pipe, characterized in that it is formed to be inclined to the reflecting surface,
The transmitted light detection type skin fluorescence measuring apparatus according to claim 14. The reflecting surface of the first light pipe and the second light pipe, characterized in that it comprises a folding reflecting surface inclined with respect to the contact surface,
The transmitted light detection type skin fluorescence measuring apparatus according to claim 14. Wherein the reflecting surface of the first light pipe and the second light pipe is mirror-coated,
The transmitted light detection type skin fluorescence measuring apparatus according to claim 14. The transmitted light detection type skin fluorescence measuring device is:
A transport unit for moving the light transmission unit up and down;
The thickness indicator by measuring the distance between the two light transmitting section informs the thickness of the measurement object,
Further comprising:
The transmitted light detection type skin fluorescence measuring apparatus according to claim 2. The contact surface of the light transmitting unit may further comprise an optical coupling portion in contact with the measurement object,
The transmitted light detection type skin fluorescence measuring apparatus according to claim 2. It said optical coupling part is characterized by constituting a coupling layer made of a liquid material or elastic material between the measurement object and the light transmitting portion,
The transmitted light detection type skin fluorescence measuring apparatus according to claim 20. The switching control unit, respectively the transmitted light signal with respect to the first light source and the second fluorescent signal and the second light source and the transmitted light signal with respect to the first light source continuously repeated the process of light source sequentially turning on and off Characterized in that it is configured to detect,
The transmitted light detection type skin fluorescence measuring apparatus according to any one of claims 1 to 21 . Wherein the first light source and the optical path of the second light source, characterized in that it is configured such that the reference sample and the measurement object is positioned selectively,
The transmitted light detection type skin fluorescence measuring apparatus according to any one of claims 1 to 21. The first light source emits light of 370 nm ± 20 nm,
The transmitted light detection type skin fluorescence measuring apparatus according to any one of claims 1 to 21. The second light source emits light of 440 nm ± 20 nm,
The transmitted light detection type skin fluorescence measuring apparatus according to any one of claims 1 to 21. The switching control unit before turning on the first, second light sources, and controls so that the said first light source the second light source is turned off both,
The transmitted light detection type skin fluorescence measuring apparatus according to any one of claims 1 to 21. If the switching control unit were both off the first and second light sources, the dark and in the first optical detector and the second light detector to measure the dark signal, the calculating unit was measured storing the signal, and for compensating for the fluorescence signal and the transmitted light signal detected from the stored dark signal,
The transmitted light detection type skin fluorescence measuring apparatus according to claim 26 . The switching control unit is characterized in that the first light source unit and the second light source unit is controlled to repeat on and off at a cycle of 10-100 Hz,
The transmitted light detection type skin fluorescence measuring apparatus according to any one of claims 1 to 21. The transmitted light detection type measurement apparatus further comprising a photodetector switching control unit for controlling said first photodetector and said second photodetector on / off,
The transmitted light detection type skin fluorescence measuring apparatus according to any one of claims 1 to 21. The transmitted light detection type skin fluorescence measuring device is:
The first light source, the second light source, and an optical sensor that includes the first optical detector, and said second optical detector,
A main body configured to be electrically connectable to the optical sensor and including the arithmetic unit;
Characterized by being separated into
The transmitted light detection type skin fluorescence measuring apparatus according to any one of claims 1 to 21. 31. The transmitted light detection type skin fluorescence measurement apparatus according to claim 30 , wherein the optical sensor includes a memory for storing detected information. The transmitted light detection type skin fluorescence measuring device is:
The first light source, the second light source, and an optical sensor that includes the first optical detector, and said second optical detector,
A main body configured to be electrically connectable to the optical sensor and including the arithmetic unit;
Is configured separately .
Wherein the optical sensor, a first fixing portion connected to the first and second light sources, the second fixing portion connected to the second photodetector and the first photodetector is formed,
The second fixing portion and the first fixing portion is opposed, and forming an insertion space therebetween,
The transmitted light detection type skin fluorescence measuring apparatus according to any one of claims 1 to 21 . The transmitted light detection type skin fluorescence measuring device is:
The first light source, the second light source, the second light source, and an optical sensor including a first optical detector, and the second optical detector,
A main body configured to be electrically connectable to the optical sensor and including the arithmetic unit;
Is configured separately .
The optical sensor includes a common light source light guide for commonly transmitting light emitted from the first light source and the second light source.
The transmitted light detection type skin fluorescence measuring apparatus according to any one of claims 1 to 21 . The optical sensor includes a common detection light guide that transmits transmitted light and skin fluorescence to the first photodetector and the second photodetector in common.
34. The transmitted light detection type skin fluorescence measuring apparatus according to claim 33 . In the optical sensor, a first dichroic mirror is installed on an optical path so as to transmit each light emitted from the first light source and the second light source to the common light source light guide.
34. The transmitted light detection type skin fluorescence measuring apparatus according to claim 33 . In the optical sensor, a second dichroic mirror is installed on an optical path so that the light transmitted from the common detection light guide is separated and transmitted to the first photodetector and the second photodetector. Characterized by the
36. The transmitted light detection type skin fluorescence measurement apparatus according to claim 35 . Between the first dichroic mirror and the first light source, the light of the first wavelength emitted from the first light source to pass through, the light of the second wavelength emitted from the first light source first suppresses One light source filter is installed,
36. The transmitted light detection type skin fluorescence measurement apparatus according to claim 35 . The first and the first light sources and the first dichroic mirror are focused between the first light source and the first dichroic mirror, and between the second light source and the first dichroic mirror . Each of the second objective lenses is installed,
36. The transmitted light detection type skin fluorescence measurement apparatus according to claim 35 . Between the second dichroic mirror and the first photodetector, a first detection filter is provided that transmits light of the first wavelength and suppresses light of the second wavelength,
Between the second dichroic mirror and the second photodetector, a second detection filter that suppresses light of the first wavelength and transmits light of the second wavelength is installed.
The transmitted light detection type skin fluorescence measuring apparatus according to claim 36 . Between the first photodetector and the second dichroic mirror and between the second photodetector and the second dichroic mirror, the light that has passed through the second dichroic mirror is reflected in the first photodetector. And a third objective lens and a fourth objective lens for focusing on the second photodetector, respectively.
The transmitted light detection type skin fluorescence measuring apparatus according to claim 36 . The transmitted light detection type skin fluorescence measuring device is:
The first light source, the second light source, and an optical sensor that includes the first optical detector, and said second optical detector,
A main body configured to be electrically connectable to the optical sensor and including the arithmetic unit;
Is configured separately .
The optical sensor includes a first light source light guide that transmits light emitted from the first light source and a second light source light guide that transmits light emitted from the second light source.
The transmitted light detection type skin fluorescence measuring apparatus according to claim 1. The optical sensor includes a first detection light guide for transmitting transmitted light and skin fluorescence to the first photodetector, and a second detection light guide for transmitting to the second photodetector.
The transmitted light detection type skin fluorescence measuring apparatus according to claim 41 . Wherein the first wavelength light emitted from the first light source is provided between the first light source and the first light source light guide to pass through, the light of the second wavelength emitted from the first light source to suppress the light source A filter is installed,
The transmitted light detection type skin fluorescence measuring apparatus according to claim 41 . A first detection filter is provided between the first light source light guide and the first light detector to pass light of the first wavelength and suppress light of the second wavelength, and the second light source light guide and A second detection filter that suppresses light of the first wavelength and transmits light of the second wavelength is installed between the second photodetector and the second photodetector.
43. The transmitted light detection type skin fluorescence measurement apparatus according to claim 42 . Wherein the end of the first fixing part is installed the first and second light sources, the first light source and the second light source is configured to irradiate light directly to the measurement target,
Wherein said first photodetector and said second photodetector is installed in the end of the second fixing portion,
Characterized in that it is configured to detect the direct transmission light and skin fluorescence in the first optical detector and the second optical detector,
The transmitted light detection type skin fluorescence measurement apparatus according to claim 32 . The first photodetector and the second photodetector have a band for dividing the first wavelength (λ1) and the second wavelength (λ2) before the two sectors of the photodetector composed of two sectors. Each filter is located,
The transmitted light detection type skin fluorescence measurement apparatus according to claim 45 . Wherein said second fixing portion and the first fixing portion, characterized in that it is manufactured with a clip form so as to fix in a state of pressurizing the measurement target,
The transmitted light detection type skin fluorescence measurement apparatus according to claim 45 . A movable standard specimen is attached to the optical sensor, and the standard specimen is inserted into the insertion space when the object to be measured is removed from the insertion space between the first fixing part and the second fixing part. It moves to be located,
The transmitted light detection type skin fluorescence measurement apparatus according to claim 32 . The optical sensor performs a measurement on the skin when the skin of the measurement target into the insertion space is located, to perform measurements on reference sample when the measurement target is removed and reference sample located in the insertion space Characterized by the
49. The transmitted light detection type skin fluorescence measurement apparatus according to claim 48 . It said optical sensor, and stores the result measured for the skin and the reference sample of the measurement target, is to transmit the detected information to the main body for storing skin and reference sample correction by the arithmetic unit Characterized in that it is configured to calculate a skin fluorescence value,
50. The transmitted light detection type skin fluorescence measurement apparatus according to claim 49 . The main body further includes a display unit,
The display unit outputs the corrected skin fluorescence signal calculated by the calculation unit,
The transmitted light detection type skin fluorescence measuring apparatus according to any one of claims 1 to 21. The transmitted light detection type skin fluorescence measurement apparatus according to any one of claims 1 to 21, wherein the calculation unit calculates a skin fluorescence value AF _corr corrected by the following mathematical formula.
AF _corr = K [I (λ2, t1) / I ₀ (λ2, t1)] / {[T (λ1)] ^k1 [T (λ2)]} ^k2
Where
T (λ1) = I (λ1, t1) / I ₀ (λ1, t1): Diffuse transmission coefficient at excitation wavelength λ1, time t1 T (λ2) = I (λ2, t2) / I ₀ (λ2, t2) : Diffuse transmission coefficient at radiation wavelength λ2, time t2 I (λ2, t1): intrinsic fluorescence (skin fluorescence) signal value of skin tissue at radiation wavelength λ2, time t1 I (λ1, t1): excitation light wavelength λ1, Transmitted light signal value of skin tissue at time t1 I (λ2, t2): Synchrotron radiation wavelength λ2, transmitted light signal value of skin tissue at time t2 , k1, k2: Exponential coefficient of calibration function for excitation light and synchrotron radiation wavelength I ₀ (λ2, t1): Intrinsic fluorescence signal value at standard specimen at synchrotron radiation wavelength λ2, time t1 I ₀ (λ1, t1): Transmitted light signal of standard specimen at excitation light wavelength λ1, time t1 Value I ₀ (λ2, t2): Transmitted light signal value of standard specimen at synchrotron radiation wavelength λ2, time t2 K: Used It is a ratio factor that takes into account the characteristics of the standard specimen .